CN100399980C - Ocular aberration correction taking into account fluctuations dueto biophysical rhythms - Google Patents
Ocular aberration correction taking into account fluctuations dueto biophysical rhythms Download PDFInfo
- Publication number
- CN100399980C CN100399980C CNB018201326A CN01820132A CN100399980C CN 100399980 C CN100399980 C CN 100399980C CN B018201326 A CNB018201326 A CN B018201326A CN 01820132 A CN01820132 A CN 01820132A CN 100399980 C CN100399980 C CN 100399980C
- Authority
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- China
- Prior art keywords
- vision
- aberration
- wave
- lens
- aberration correction
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- Legal status (The legal status is an assumption and is not a legal conclusion. Google has not performed a legal analysis and makes no representation as to the accuracy of the status listed.)
- Expired - Lifetime
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Classifications
-
- A—HUMAN NECESSITIES
- A61—MEDICAL OR VETERINARY SCIENCE; HYGIENE
- A61B—DIAGNOSIS; SURGERY; IDENTIFICATION
- A61B3/00—Apparatus for testing the eyes; Instruments for examining the eyes
- A61B3/10—Objective types, i.e. instruments for examining the eyes independent of the patients' perceptions or reactions
-
- G—PHYSICS
- G02—OPTICS
- G02C—SPECTACLES; SUNGLASSES OR GOGGLES INSOFAR AS THEY HAVE THE SAME FEATURES AS SPECTACLES; CONTACT LENSES
- G02C7/00—Optical parts
- G02C7/02—Lenses; Lens systems ; Methods of designing lenses
- G02C7/04—Contact lenses for the eyes
-
- A—HUMAN NECESSITIES
- A61—MEDICAL OR VETERINARY SCIENCE; HYGIENE
- A61B—DIAGNOSIS; SURGERY; IDENTIFICATION
- A61B3/00—Apparatus for testing the eyes; Instruments for examining the eyes
- A61B3/10—Objective types, i.e. instruments for examining the eyes independent of the patients' perceptions or reactions
- A61B3/1015—Objective types, i.e. instruments for examining the eyes independent of the patients' perceptions or reactions for wavefront analysis
-
- G—PHYSICS
- G02—OPTICS
- G02C—SPECTACLES; SUNGLASSES OR GOGGLES INSOFAR AS THEY HAVE THE SAME FEATURES AS SPECTACLES; CONTACT LENSES
- G02C7/00—Optical parts
- G02C7/02—Lenses; Lens systems ; Methods of designing lenses
- G02C7/024—Methods of designing ophthalmic lenses
- G02C7/028—Special mathematical design techniques
-
- G—PHYSICS
- G02—OPTICS
- G02C—SPECTACLES; SUNGLASSES OR GOGGLES INSOFAR AS THEY HAVE THE SAME FEATURES AS SPECTACLES; CONTACT LENSES
- G02C2202/00—Generic optical aspects applicable to one or more of the subgroups of G02C7/00
- G02C2202/22—Correction of higher order and chromatic aberrations, wave front measurement and calculation
Abstract
The invention provides correction of wavefront aberrations of the eye that take into account fluctuations in the aberrations due to biophysical rhythms. Correction is provided for an intermediate value of these fluctuations of the wavefront aberrations. This intermediate value is determined by extrapolating a wavefront measurement to predict the overall variation. The final correction is determined using a weighting scheme derived from the clinical comparisons of the frequency and amplitude components of the variations.
Description
Technical field
The present invention relates to the rectification of vision aberration.Especially, the invention provides rectification, wherein consider the aberration fluctuation that causes because of the biophysical rhythm and pace of moving things the eyes wave front aberration.
Background technology
The method and the instrument that use Wavefront sensor to measure the aberration of eyes are known.Known device can be measured, the optical wavefront of estimation, interpolation or computation vision.Then, thus the aberration measured value by mathematics be converted to difference in height and provide an absolute altitude figure above and below specified average regional value, promptly known optical path difference.The rectification of aberration can be by introducing optical path difference, or the aberration inverse filter finishes, and they are used for compensating because the distortion that the aberration of vision causes.These rectifications can be incorporated the design of eyeglass into and provide visual acuity to correct.
The shortcoming of correcting aberration according to the wavefront measurement data is not have to consider by the fluctuation in time of the caused described aberration of the biophysical rhythm and pace of moving things.So, need a kind of according to the method for the biophysical rhythm and pace of moving things according to wave-front optical aberration measurement design data ophthalmic lens.
Detailed description of the invention and preferred embodiment
The ophthalmic lens that the invention provides a kind of method and utilize this method to make, described method have considered when calculating the aberration correction amount because the fluctuation of the vision wave-front optical aberration measurement value that the biophysical rhythm and pace of moving things causes.This method is used for providing repeatably when determining accurate aberration correction amount and measured value reliably.
In one embodiment, the invention provides a kind of method for designing of correcting individual visual acuity, comprise, constitute by following steps basically: the measured value that a.) obtains the vision wave front aberration of an eye through sufficient computation time; B.) determine frequency component and the amplitude component of vision wave-front optical aberration measurement value in cyclical movement; And c.) the one or more vision wavefront aberration calculation for an eye go out vision wave-front aberration correction value, consider the cyclically-varying of human eye aberration in the time of calculating.In another embodiment, the invention provides the ophthalmic lens that utilizes method of the present invention to produce.
Here " ophthalmic lens (ophthalmic lens) " means flexible focal length lenses, contact lens, and intraocular lens covers lens etc.Preferably, lens of the present invention are contact lenses.Here " vision wavefront " means the wavefront that forms before the eye.Here " vision wave front aberration " means poor that the wavefront that forms before the eyes compares with desirable wavefront.The instrument of finishing aberration measurement includes but not limited to, aberroscope, and by the device of point or straight line distribution measuring vision modulation transfer function (MTF), or any measurement, estimation, the similar device of interpolation or computation vision wavefront.Employed device must have can capture because the sensitivity that the aberration that biophysics's rhythm and pace of moving things causes changes it.The device that is fit to is commercially available, for example the Model G200 of Wavefront Sciences company.
The present invention finds that cyclical movement or fluctuation occur in the high-order and the low order of an eye wave-front optical aberration measurement value, and its biophysics's cycle with the individual is relevant, i.e. Ge Ren cycle period and breathing cycle.Because these change the not significantly effect of individual vision, therefore needn't utilize the ultimate value of described variation to carry out aberration correction.But correct amount must be the intermediate value that wave front aberration changes.If supposition cyclical movement exists, this intermediate value is determined easily so, thereby and utilizes this knowledge that whole variations is predicted in the wave front aberration extrapolation.Then utilize frequency component and amplitude component to carry out the objective weighting scheme that relatively obtains and determine individual last correct amount to changing.
In the initial step of method of the present invention, obtain or measure individual's vision wave front aberration through the sufficient time on calculating.The wave-front optical aberration measurement that described " sufficient time in the calculating " means described vision is to be enough to observe a certain amount of owing to carry out in the time period of the wave front aberration fluctuation that the biophysics causes in the cycle, and described amount can calculate the frequency and the amplitude of described fluctuation.This time period is preferably enough captures or in order to finish, in biophysics's cycle that at least one is complete, promptly the described cycle comprises complete breathing cycle and cycle period.
For example, in order to sample to influential cycle period of wave front aberration or pulse (pulse) cycle, described individual's aberration measurement can be by capturing 10 at 5 hertz image and carry out; For in the breathing cycle of sampling to effect through 20 images of total of 35 seconds, capture other 10 at 0.3 hertz image.The data of the required minimum of the frequency of calculating wavefront variation and amplitude approximately are provided through 20 images of 35 seconds usually, at least.Yet ideal concrete quantity depends on individuality to be measured.
In addition, the abundant sampling of the wavefront measurement value of crowd's vision can be determined the mode of described fluctuation usually.Utilize this information, thereby only need determine the position of individual on described colony change curve to record the enough wave front data points of individual wave-front optical aberration measurement a period of time of unknown individual vision.Usually, each time in breathing cycle and the cycle period about 5 to 10 points become the point of sufficient amount.Remaining desired data can infer out by the previous feature according to colony's sample.For example, the leak source in each cycle can carry out interpolation, and the cycle portions of perhaps not measuring can obtain by interpolation.
In order to carry out wave-front optical aberration measurement, tested eyes do not have mydriasis or anesthesia.And described wavefront information is preferably with the form record of image.Can transform with software and change described wavefront image into suitable form form and show with diagrammatic form according to the original state that is recorded.Suitable software includes but not limited to utilize the full gloss analysis software-2D (Complete Light Analysis Software-2D) of wavefront theory (Wavefront Sciences) and the analysis software (Complete Ophthalmic Analysis Software) of full ophthalmology.The appropriate format of selecting depends on the data that plan is used.For example, initial data can be converted into Taylor (Taylor) or Zernike (Zernike) multinomial, clinical specific refraction data that calculate and iso-focal power (iso-power), and the pseudo-colours and the optical path difference absolute altitude figure of 3 dimensions can obtain.
In next step of method of the present invention, the frequency of each cyclical movement and amplitude component can be obtained by arbitrary suitable method in the wave-front optical aberration measurement value of vision.For example, aberration can be expressed as Zernike coefficients, thereby these coefficients are analyzed the time dependent rule of described coefficient through fast Fourier transform respectively.Described transformed value then is combined into rectangular histogram and immediate time of obtaining from described rectangular histogram is primary period in the coefficient.In most cases, have two cycles, one for circulate fast the rhythm and pace of moving things another be more at a slow speed respiratory rhythm.Described amplitude is directly determined by the maximum and the minima of initial data.
Subsequently, the wave-front aberration correction value of vision after consideration the cycle change and calculated.In this step, the weighted sum of individual frequency component is used to derive the correction value of aberration.Many methods can be used to carry out above-mentioned steps.For example, in measuring at interval, all measured value can be averaged, or is integrated.In the simplest form of taking the mean, image is accumulated, and for example accumulates 20 images in through 35 seconds time.The 3rd rank item that calculating defocuses, 45 degree and 90 degree are astigmatic, coma-x, coma-y, zernike term such as trilobal astigmatism and spherical aberration obtain comprising 7 groups of items of 20 data points.
Clinical assays individual's specific refraction and obtain actual defocus and the measured value of astigmatism value and these visual acuitys is compared with the wavefront measured value.This just can obtain a human visual system and handle periodically variable method.On the other hand, thus the specific refraction that can measure colony obtains data predicts the processing of a human visual system to cyclical movement according to these data.Sphere only, astigmatism and angle can record clinically.Yet, can suppose that more higher order aberratons can be handled by same mode by visual system.
If the dependency of clinical data and wave front data statistics shows when the wavefront aberration data that occurs in vision when best correlation is averaged as time function, this arithmetic average can be calculated and meansigma methods can be used as the aberration correction value every sets of data.Described in addition statistic correlation will be used to find out other functions that described clinical research and described wave front data the best are got in touch.
Described aberration measurement value mathematically becomes difference in height, and a kind of absolute altitude figure that specifies the average sphere value, the just optical path difference known to of being higher or lower than so just is provided.The correct amount of aberration is provided by the optical path difference of introducing or aberration inverse filtering, and it compensates the distortion that the vision aberration causes.
The optical path difference of described conversion can be used to be provided as the wearer and designs a kind of ophthalmic lens, for example considers the optical effect of correcting lens and is entered in the lens design program.Described aberration correction value can be used in front surface or rear surface or the front surface and the rear surface of described lens.Described " ophthalmic lens " means a kind of flexible focal length lenses, a kind of contact lens, a kind of intraocular lens, a kind of corneal implant lens, a kind of covering lens etc., or the combination of said lens.Preferably, lens of the present invention are contact lenses.Described aberration correction value can be used in front surface or rear surface or the front surface and the rear surface of described glasses.The used contact lens of the present invention both can be hard also can be soft lens.The preferred soft-contact lens that uses is to be made by any suitable material.Described aberration correction value can be used in front surface or rear surface or the front surface and the rear surface of described glasses.
The front surface of described contact lens or thing side, perhaps the reversing pattern absolute altitude figure that rear surface or eye side surface also can compound lens wearer corneas.Described individual's cornea pattern can be included but not limited to, by utilizing cornea pattern instrument by any known method decision.For making described soft-contact lens, at first be used to the state of the non-bending of the lens model under the non-complete case of bending in described elevation data of starting stage.Then, when described lens are positioned over human eye, consider the curvature of described SCL, described data are transformed or hold (wrap).The absolute altitude and the effect that surrounds when utilizing the cornea topographic data of described cornea are described thus.Described curvature translation data then is mapped on computer numerical control (CNC) grid chart, and the surface that is used to make described lens or mould instrument.
Described ophthalmic lens of the present invention can be made by any known means for ophthalmic lens manufacture.For example, the contact lens of described invention can be formed by any conventional method, and these methods include but not limited to the diamond turning of mould, and it is used to form lens of the present invention.Subsequently, suitable liquid resin is placed between the described mould then by compression and solidifies described resin formation lens of the present invention.In addition, described contact lens surfaces can utilize diamond turning to be converted to button-type lens (lens buttons).
Any known material that is suitable for making ophthalmic lens can be used for making lens of the present invention.Preferably, the embodiment of contact lens, the material that is used to form described lens of the present invention can be any known material hard or soft-contact lens that is used to produce.Preferably, be a kind of material of suitable manufacturing soft-contact lens for forming the selected material of lens of the present invention.The suitable material that utilizes method of the present invention to form above-mentioned contact lens includes but not limited to, silicone elastomer comprises the macromole of silicone, the described macromole that comprises silicone includes but not limited to, at U.S. Patent number 5,371,147,5,314, those disclosed in 960 and 5,057,578, they are reference here in the lump, also comprise hydrogel, comprise the macromole such as hydrogel of silicone etc., and their combination.More preferably, the surface is a siloxanes, or comprise silicone functionalities, include but not limited to the polydimethylsiloxane macromole, methacryloxypropyl polyalkyl siloxanes (methacryloxypropyl polyalkyl siloxanes), and composition thereof, the hydrogel of silicon hydrogel or a kind of for example etafilcon A.
Claims (8)
1. a design individual visual acuity corrigent method comprises the steps: a.) obtain the measured value of wave front aberration of the vision of an eye through the sufficient time on calculating; B.) determine frequency component and the amplitude component of vision wave-front optical aberration measurement value in cyclical movement; And c.) the one or more vision wavefront aberration calculation for an eye go out vision wave-front aberration correction value, consider the cyclically-varying of human eye aberration in the time of calculating.
2. method as claimed in claim 1 is characterized in that the sufficient time in the described calculating is the necessary time of finishing biophysics's cycle.
3. method as claimed in claim 1, wherein step b.) to implement by following steps: the wave front aberration that vision i.) is provided is as Zernike coefficients; Ii.) make Zernike coefficients carry out fast Fourier transform and iii.) described transformed value is combined into rectangular histogram.
4. method as claimed in claim 1, wherein step c) further comprise for the wave-front aberration correction that obtains vision and introduce optical path difference at lens front surface, rear surface or front surface and rear surface.
5. method as claimed in claim 1 further comprises steps d .) rear surface of lens and individual cornea pattern are complementary.
6. method as claimed in claim 1 further comprises steps d .) front surface of lens and individual cornea pattern are complementary.
7. method as claimed in claim 5 further is included as the wave-front aberration correction of finishing vision and changes at the lens front surface combination elevation angle.
8. method as claimed in claim 6 further is included as the wave-front aberration correction of finishing vision and changes at the lens front surface combination elevation angle.
Applications Claiming Priority (2)
| Application Number | Priority Date | Filing Date | Title |
|---|---|---|---|
| US09/732,637 | 2000-12-08 | ||
| US09/732,637 US6547391B2 (en) | 2000-12-08 | 2000-12-08 | Ocular aberration correction taking into account fluctuations due to biophysical rhythms |
Publications (2)
| Publication Number | Publication Date |
|---|---|
| CN1849091A CN1849091A (en) | 2006-10-18 |
| CN100399980C true CN100399980C (en) | 2008-07-09 |
Family
ID=24944366
Family Applications (1)
| Application Number | Title | Priority Date | Filing Date |
|---|---|---|---|
| CNB018201326A Expired - Lifetime CN100399980C (en) | 2000-12-08 | 2001-12-10 | Ocular aberration correction taking into account fluctuations dueto biophysical rhythms |
Country Status (13)
| Country | Link |
|---|---|
| US (1) | US6547391B2 (en) |
| EP (2) | EP1343413B1 (en) |
| JP (1) | JP4216070B2 (en) |
| KR (1) | KR100906084B1 (en) |
| CN (1) | CN100399980C (en) |
| AR (1) | AR031903A1 (en) |
| AU (2) | AU2002227393B2 (en) |
| BR (1) | BR0116048B1 (en) |
| CA (1) | CA2430873C (en) |
| DE (2) | DE60129735T2 (en) |
| HK (1) | HK1055665A1 (en) |
| TW (1) | TW533064B (en) |
| WO (1) | WO2002045577A1 (en) |
Families Citing this family (41)
| Publication number | Priority date | Publication date | Assignee | Title |
|---|---|---|---|---|
| SE0004829D0 (en) * | 2000-12-22 | 2000-12-22 | Pharmacia Groningen Bv | Methods of obtaining ophthalmic lenses providing the eye with reduced aberrations |
| CA2498717A1 (en) * | 2002-09-13 | 2004-03-25 | Ocular Sciences, Inc. | Devices and methods for improving vision |
| WO2004034129A1 (en) * | 2002-10-04 | 2004-04-22 | Carl Zeiss Ag | Method for production of a lens and lens produced thus |
| SE0203564D0 (en) * | 2002-11-29 | 2002-11-29 | Pharmacia Groningen Bv | Multifocal opthalmic lens |
| US7896916B2 (en) | 2002-11-29 | 2011-03-01 | Amo Groningen B.V. | Multifocal ophthalmic lens |
| US8911086B2 (en) | 2002-12-06 | 2014-12-16 | Amo Manufacturing Usa, Llc | Compound modulation transfer function for laser surgery and other optical applications |
| US8596787B2 (en) | 2003-06-20 | 2013-12-03 | Amo Manufacturing Usa, Llc | Systems and methods for prediction of objective visual acuity based on wavefront measurements |
| CA2529813C (en) * | 2003-06-20 | 2015-11-17 | Visx, Incorporated | Systems and methods for prediction of objective visual acuity based on wavefront measurements |
| BRPI0514349A (en) * | 2004-08-13 | 2008-06-10 | Ottawa Health Research Inst | ophthalmic vision enhancing devices and related methods and compositions |
| US7922326B2 (en) | 2005-10-25 | 2011-04-12 | Abbott Medical Optics Inc. | Ophthalmic lens with multiple phase plates |
| US7455404B2 (en) * | 2004-10-25 | 2008-11-25 | Advanced Medical Optics, Inc. | Ophthalmic lens with multiple phase plates |
| US20060118162A1 (en) * | 2004-12-06 | 2006-06-08 | Florida Atlantic University | Powering a vehicle and providing excess energy to an external device using photovoltaic cells |
| TWI410696B (en) * | 2005-02-15 | 2013-10-01 | Univ Queensland | Lens control of myopla |
| EP2041615A4 (en) * | 2005-11-09 | 2011-03-09 | Univ Houston | Method for designing and manufacturing custom optics |
| WO2007092550A2 (en) * | 2006-02-08 | 2007-08-16 | Coopervision Inc. | Corneal onlays and related methods |
| US7883520B2 (en) * | 2006-04-10 | 2011-02-08 | Forsight Labs, Llc | Corneal epithelial pocket formation systems, components and methods |
| US8318055B2 (en) | 2007-08-21 | 2012-11-27 | Johnson & Johnson Vision Care, Inc. | Methods for formation of an ophthalmic lens precursor and lens |
| US7905594B2 (en) * | 2007-08-21 | 2011-03-15 | Johnson & Johnson Vision Care, Inc. | Free form ophthalmic lens |
| US8317505B2 (en) | 2007-08-21 | 2012-11-27 | Johnson & Johnson Vision Care, Inc. | Apparatus for formation of an ophthalmic lens precursor and lens |
| US8313828B2 (en) | 2008-08-20 | 2012-11-20 | Johnson & Johnson Vision Care, Inc. | Ophthalmic lens precursor and lens |
| US20090219485A1 (en) * | 2008-02-29 | 2009-09-03 | Sarver Edwin J | Ocular wavefront system |
| US9417464B2 (en) | 2008-08-20 | 2016-08-16 | Johnson & Johnson Vision Care, Inc. | Method and apparatus of forming a translating multifocal contact lens having a lower-lid contact surface |
| US20100087920A1 (en) * | 2008-10-07 | 2010-04-08 | Forsight Labs, Llc | Corneal Onlay Lenses and Related Methods for Improving Vision of Presbyopic Patients |
| US8240849B2 (en) | 2009-03-31 | 2012-08-14 | Johnson & Johnson Vision Care, Inc. | Free form lens with refractive index variations |
| US8807076B2 (en) | 2010-03-12 | 2014-08-19 | Johnson & Johnson Vision Care, Inc. | Apparatus for vapor phase processing ophthalmic devices |
| TWI588560B (en) | 2012-04-05 | 2017-06-21 | 布萊恩荷登視覺協會 | Lenses, devices, methods and systems for refractive error |
| EP3824798A1 (en) | 2012-08-31 | 2021-05-26 | Amo Groningen B.V. | Multi-ring lens, systems and methods for extended depth of focus |
| US9201250B2 (en) | 2012-10-17 | 2015-12-01 | Brien Holden Vision Institute | Lenses, devices, methods and systems for refractive error |
| EP2908773B1 (en) | 2012-10-17 | 2024-01-03 | Brien Holden Vision Institute | Lenses, devices, methods and systems for refractive error |
| US9645412B2 (en) | 2014-11-05 | 2017-05-09 | Johnson & Johnson Vision Care Inc. | Customized lens device and method |
| CA2969608A1 (en) * | 2014-12-04 | 2016-06-09 | Amo Groningen B.V. | Apparatus, systems and methods for improving visual outcomes for pseudophakic patients |
| US10359643B2 (en) | 2015-12-18 | 2019-07-23 | Johnson & Johnson Vision Care, Inc. | Methods for incorporating lens features and lenses having such features |
| EP3413839A1 (en) | 2016-02-09 | 2018-12-19 | AMO Groningen B.V. | Progressive power intraocular lens, and methods of use and manufacture |
| IT201600097763A1 (en) * | 2016-09-29 | 2018-03-29 | Sifi Medtech Srl | LENS FOR ASTIGMATISM |
| AU2018235011A1 (en) | 2017-03-17 | 2019-10-24 | Amo Groningen B.V. | Diffractive intraocular lenses for extended range of vision |
| US11523897B2 (en) | 2017-06-23 | 2022-12-13 | Amo Groningen B.V. | Intraocular lenses for presbyopia treatment |
| WO2019002384A1 (en) | 2017-06-28 | 2019-01-03 | Amo Groningen B.V. | Diffractive lenses and related intraocular lenses for presbyopia treatment |
| EP3639084A1 (en) | 2017-06-28 | 2020-04-22 | Amo Groningen B.V. | Extended range and related intraocular lenses for presbyopia treatment |
| US11327210B2 (en) | 2017-06-30 | 2022-05-10 | Amo Groningen B.V. | Non-repeating echelettes and related intraocular lenses for presbyopia treatment |
| AU2020416055A1 (en) | 2019-12-30 | 2022-08-25 | Amo Groningen B.V. | Lenses having diffractive profiles with irregular width for vision treatment |
| US11364696B2 (en) | 2020-09-18 | 2022-06-21 | Johnson & Johnson Vision Care, Inc | Apparatus for forming an ophthalmic lens |
Citations (5)
| Publication number | Priority date | Publication date | Assignee | Title |
|---|---|---|---|---|
| CN1098276A (en) * | 1993-08-01 | 1995-02-08 | 徐渊 | A kind of range finding retinoscopy optometry method and instrument |
| CN1101249A (en) * | 1994-06-24 | 1995-04-12 | 中国科学院上海技术物理研究所 | Real time collecting for eyeground picture and processing method and its apparatus |
| WO1998027863A1 (en) * | 1996-12-23 | 1998-07-02 | University Of Rochester | Apparatus for improving vision and resolution of retinal images |
| CN1255319A (en) * | 1998-12-02 | 2000-06-07 | 贺极苍 | Aberration measuring instrument for human eyes and its measuring method |
| US6086204A (en) * | 1999-09-20 | 2000-07-11 | Magnante; Peter C. | Methods and devices to design and fabricate surfaces on contact lenses and on corneal tissue that correct the eye's optical aberrations |
Family Cites Families (4)
| Publication number | Priority date | Publication date | Assignee | Title |
|---|---|---|---|---|
| US5057578A (en) | 1990-04-10 | 1991-10-15 | E. I. Du Pont De Nemours And Company | Silicone-containing block copolymers and macromonomers |
| US5314960A (en) | 1990-04-10 | 1994-05-24 | Permeable Technologies, Inc. | Silicone-containing polymers, oxygen permeable hydrophilic contact lenses and methods for making these lenses and treating patients with visual impairment |
| US5371147A (en) | 1990-10-11 | 1994-12-06 | Permeable Technologies, Inc. | Silicone-containing acrylic star polymers, block copolymers and macromonomers |
| US6199986B1 (en) | 1999-10-21 | 2001-03-13 | University Of Rochester | Rapid, automatic measurement of the eye's wave aberration |
-
2000
- 2000-12-08 US US09/732,637 patent/US6547391B2/en not_active Expired - Lifetime
-
2001
- 2001-12-07 AR ARP010105700A patent/AR031903A1/en active IP Right Grant
- 2001-12-07 TW TW090130273A patent/TW533064B/en not_active IP Right Cessation
- 2001-12-10 AU AU2002227393A patent/AU2002227393B2/en not_active Expired
- 2001-12-10 DE DE60129735T patent/DE60129735T2/en not_active Expired - Lifetime
- 2001-12-10 WO PCT/US2001/048245 patent/WO2002045577A1/en active IP Right Grant
- 2001-12-10 CN CNB018201326A patent/CN100399980C/en not_active Expired - Lifetime
- 2001-12-10 AU AU2739302A patent/AU2739302A/en active Pending
- 2001-12-10 DE DE60140331T patent/DE60140331D1/en not_active Expired - Lifetime
- 2001-12-10 EP EP01996244A patent/EP1343413B1/en not_active Expired - Lifetime
- 2001-12-10 CA CA2430873A patent/CA2430873C/en not_active Expired - Lifetime
- 2001-12-10 BR BRPI0116048-6A patent/BR0116048B1/en not_active IP Right Cessation
- 2001-12-10 EP EP07075182A patent/EP1797815B1/en not_active Expired - Lifetime
- 2001-12-10 JP JP2002547371A patent/JP4216070B2/en not_active Expired - Lifetime
- 2001-12-10 KR KR1020037007694A patent/KR100906084B1/en active IP Right Grant
-
2003
- 2003-11-06 HK HK03108036A patent/HK1055665A1/en not_active IP Right Cessation
Patent Citations (5)
| Publication number | Priority date | Publication date | Assignee | Title |
|---|---|---|---|---|
| CN1098276A (en) * | 1993-08-01 | 1995-02-08 | 徐渊 | A kind of range finding retinoscopy optometry method and instrument |
| CN1101249A (en) * | 1994-06-24 | 1995-04-12 | 中国科学院上海技术物理研究所 | Real time collecting for eyeground picture and processing method and its apparatus |
| WO1998027863A1 (en) * | 1996-12-23 | 1998-07-02 | University Of Rochester | Apparatus for improving vision and resolution of retinal images |
| CN1255319A (en) * | 1998-12-02 | 2000-06-07 | 贺极苍 | Aberration measuring instrument for human eyes and its measuring method |
| US6086204A (en) * | 1999-09-20 | 2000-07-11 | Magnante; Peter C. | Methods and devices to design and fabricate surfaces on contact lenses and on corneal tissue that correct the eye's optical aberrations |
Also Published As
| Publication number | Publication date |
|---|---|
| JP4216070B2 (en) | 2009-01-28 |
| KR100906084B1 (en) | 2009-07-07 |
| DE60129735T2 (en) | 2008-05-08 |
| TW533064B (en) | 2003-05-21 |
| DE60140331D1 (en) | 2009-12-10 |
| JP2004526475A (en) | 2004-09-02 |
| EP1343413A1 (en) | 2003-09-17 |
| CA2430873A1 (en) | 2002-06-13 |
| US20020071097A1 (en) | 2002-06-13 |
| CA2430873C (en) | 2010-09-14 |
| WO2002045577A1 (en) | 2002-06-13 |
| CN1849091A (en) | 2006-10-18 |
| BR0116048A (en) | 2003-10-14 |
| AU2739302A (en) | 2002-06-18 |
| BR0116048B1 (en) | 2011-09-20 |
| AU2002227393B2 (en) | 2005-07-21 |
| EP1797815A3 (en) | 2007-11-28 |
| KR20030060983A (en) | 2003-07-16 |
| EP1343413B1 (en) | 2007-08-01 |
| US6547391B2 (en) | 2003-04-15 |
| EP1797815B1 (en) | 2009-10-28 |
| EP1797815A2 (en) | 2007-06-20 |
| AR031903A1 (en) | 2003-10-08 |
| HK1055665A1 (en) | 2004-01-21 |
| DE60129735D1 (en) | 2007-09-13 |
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